Sensor device with OLED

ABSTRACT

A sensor device configured to be attached to a drug delivery device and configured to illuminate the drug delivery device when attached, the sensor device having an OLED having a transparent first electrode, a transparent second electrode and a central layer disposed between the first and second electrodes, the central layer comprising at least one organic layer, the at least one organic layer configured to emit light through the transparent first electrode, and an optical sensor arranged to receive light reflected from a surface of the drug delivery device, wherein the central layer of the OLED has a region without the at least one organic layer and wherein the optical sensor is arranged, when the sensor device is attached to the drug delivery device, to view a predetermined area of the surface of the drug delivery device through the region without the at least one organic layer.

CROSS REFERENCE TO RELATED APPLICATIONS

The present application is a continuation of U.S. patent applicationSer. No. 14/783,170 filed Oct. 8, 2015, which is a U.S. National PhaseApplication pursuant to 35 U.S.C. § 371 of International Application No.PCT/EP2014/057785 filed Apr. 16, 2014, which claims priority to EuropeanPatent Application No. 13164752.1 filed Apr. 22, 2013. The entiredisclosure contents of these applications are herewith incorporated byreference into the present application.

TECHNICAL FIELD

The present invention relates to a sensor device for attachment to adrug delivery device, where the sensor device contains an OLED.

BACKGROUND

A variety of diseases exists that require regular treatment by injectionof a medicament. Such injection can be performed by using injectiondevices, which are applied either by medical personnel or by patientsthemselves. As an example, type-1 and type-2 diabetes can be treated bypatients themselves by injection of insulin doses, for example once orseveral times per day. For instance, a pre-filled disposable insulin pencan be used as an injection device. Alternatively, a re-usable pen maybe used. A re-usable pen allows replacement of an empty medicamentcartridge by a new one. Either pen may come with a set of one-wayneedles that are replaced before each use. The insulin dose to beinjected can then for instance be manually selected at the insulin penby turning a dosage knob and observing the actual dose from a dosewindow, dose number indicator, or display of the insulin pen. The doseis then injected by inserting the needle into a suited skin portion andpressing an injection button of the insulin pen. To be able to monitorinsulin injection, for instance to prevent false handling of the insulinpen or to keep track of the doses already applied, it is desirable tomeasure information related to a condition and/or use of the injectiondevice, such as for instance information on the injected insulin typeand dose.

SUMMARY

A first aspect of the invention provides a sensor device configured tobe attached to a drug delivery device and configured to illuminate thedrug delivery device when attached, the sensor device comprising:

an OLED having a transparent first electrode, a transparent secondelectrode and a central layer disposed between the first and secondelectrodes, the central layer comprising at least one organic layer, theat least one organic layer configured to emit light through thetransparent first electrode; and

an optical sensor arranged to receive light reflected from a surface ofthe drug delivery device, wherein the central layer of the OLED has aregion without the at least one organic layer and wherein the opticalsensor is arranged, when the sensor device is attached to the drugdelivery device, to view a predetermined area of the surface of the drugdelivery device through the region without the at least one organiclayer.

The use of an OLED to produce diffuse light is advantageous as thediffuse light which is emitted from the first electrode provides evenillumination of the surface of the drug delivery device which is to beimaged by the optical sensor. Reflections, bright spots and distortionswhich may hamper the image taking process are reduced or eliminated bythe use of the OLED.

The first electrode may be an anode and the second electrode may be acathode. Alternatively, the OLED may have a top emitting structure inwhich the positions of the anode and cathode are reversed.

The sensor device may further comprise a reflective backing layeradjacent the second electrode configured to reflect any light whichescapes the OLED through the second electrode back into the OLED. Thisincreases the illumination efficiency of the OLED and consequently thepower efficiency of the sensor device.

The region without the at least one organic layer may comprise atransparent material. This allows the shape of the light emitting partof the OLED to be controlled. The optical sensor is also able to clearlyview the surface of the drug delivery device through the transparentmaterial while light within the OLED can pass through the material andbe reflected internally.

The region without the at least one organic layer may comprise a hole inthe central layer and the OLED may comprise corresponding holes in thefirst and second electrodes such that a hole is formed through the bodyof the OLED. No visual distortion of the capture images results when theoptical sensor views the drug delivery device through this hole.

The sensor device may further comprise a lens assembly configured tofocus light reflected from a surface of the drug delivery device ontothe optical sensor. This may reduce the technical requirement of theoptical sensor and allow a cheaper sensor to be used. The lens assemblymay be disposed in the hole in the OLED such that a first end of thelens assembly is the same or a smaller distance from the surface of thedrug delivery device than the first electrode. This may result in aspace saving within the sensor device and/or reduce the cost andcomplexity of the optical elements in the lens assembly. Thisarrangement may also allow a lower level of illumination to be used asthe lens assembly and optical sensor are closer to the surface of thedrug delivery device. Unwanted distortion and reflection effects mayalso be mitigated by placing the lens assembly closer to the drugdelivery device.

The sensor device may further comprise a processor configured to receivelight intensity signals from the sensor and to perform an opticalcharacter recognition process on the received signals to determine anumber present on the surface of the drug delivery device. The processormay be further configured to determine an amount of medicamentprogrammed into the drug delivery device and to cause the amount ofmedicament to be displayed on a display device of the drug deliverydevice.

The OLED may be curved. The OLED may be substantially concentric withthe surface of the drug delivery device. The curvature of the OLED maybe such that when the sensor device is attached to the drug deliverydevice, the light emitting surface (first electrode) of the OLED and thesurface of the drug delivery device are concentric or substantiallyconcentric. The second electrode of the OLED may also be concentric orsubstantially concentric with the surface of the drug delivery device.Thus, the distance between the light emitting surface and the lightreflecting surface is approximately constant across the field of view ofthe optical sensor. This results in a more homogeneous illumination ofthe drug delivery device.

The OLED may further comprise one or more brightness enhancing layers.These act to increase the illumination efficiency of the OLED andconsequently increase the power efficiency of the sensor device.

The drug delivery device may be a pen type injection device and thesurface of the drug delivery device may be a cylindrical surface.

A second aspect of the invention provides a system comprising the sensordevice of the first aspect and a drug delivery device configured to beattached to the sensor device.

Embodiments of the invention will now be described, by way of exampleonly, with reference to the accompanying drawings.

BRIEF DESCRIPTION OF THE FIGURES

The figures show:

FIG. 1a : an exploded view of an drug delivery device;

FIG. 1b shows a perspective view of some detail of the drug deliverydevice of FIG. 1;

FIG. 2a : a schematic illustration of a sensor device to be releasablyattached to the drug delivery device of FIG. 1 according to an aspect ofthe present invention;

FIG. 2b : a perspective view of a sensor device to be releasablyattached to the drug delivery device of FIG. 1 according to variousaspects of the present invention;

FIG. 2c : a perspective view of a sensor device to be releasablyattached to the drug delivery device of FIG. 1 according to otheraspects of the present invention;

FIG. 3: a schematic view of a sensor device attached to a drug deliverydevice showing components of the sensor device;

FIG. 4: an exploded view of some components of the sensor deviceaccording to embodiments of the invention;

FIG. 5a : a schematic cross-sectional view of parts of the sensor deviceand drug delivery device according to embodiments of the invention;

FIG. 5b : a schematic cross-sectional view of parts of the sensor deviceand drug delivery device according to further embodiments of theinvention;

FIG. 6: a plan view of an organic LED suitable for use in embodiments ofthe present invention

FIG. 7: an exploded view of some components of the sensor deviceaccording to embodiments of the invention;

FIG. 8: a schematic cross-sectional view of parts of the sensor deviceand drug delivery device according to further embodiments of theinvention;

FIG. 9: a flowchart of a method used in various aspects.

DETAILED DESCRIPTION

In the following, embodiments of the present invention will be describedwith reference to an insulin injection device. The present invention ishowever not limited to such application and may equally well be deployedwith injection devices that eject other medicaments, or with other typesof medical devices as well as with other types of transcutaneous drugdelivery devices and methods.

FIG. 1a is an exploded view of a drug delivery device 1, which may forinstance represent Sanofi's Solostar (R) insulin injection pen. The drugdelivery device 1 of FIG. 1 is a pre-filled, disposable injection penthat comprises a housing 10 and contains an insulin container 14, towhich a needle 15 can be affixed. The needle is protected by an innerneedle cap 16 and an outer needle cap 17, which in turn can be coveredby a cap 18. An insulin dose to be ejected from drug delivery device 1can be selected by turning the dosage knob 12, and the selected dose isthen displayed via dosage window 13, for instance in multiples ofso-called International Units (IU), wherein one IU is the biologicalequivalent of about 45.5 micrograms of pure crystalline insulin ( 1/22mg). An example of a selected dose displayed in dosage window 13 may forinstance be 30 IUs, as shown in FIG. 1a . It should be noted that theselected dose may equally well be displayed differently, for instance bymeans of an electronic display or any other type of dose numberindicator

FIG. 1b is a perspective view of the dosage knob 12 end of the drugdelivery device 1. Turning the dosage knob 12 causes a mechanical clicksound to provide acoustical feedback to a user. The numbers displayed indosage window 13 are printed on a sleeve that is contained in housing 10and mechanically interacts with a piston in insulin container 14. Whenneedle 15 is stuck into a skin portion of a patient, and then injectionbutton 11 is pushed, the insulin dose displayed in display window 13will be ejected from drug delivery device 1. When the needle 15 of drugdelivery device 1 remains for a certain time in the skin portion afterthe injection button 11 is pushed, a high percentage of the dose isactually injected into the patient's body. Ejection of the insulin dosealso causes a mechanical click sound, which is however different fromthe sounds produced when using dosage knob 12.

The housing 10 of the drug delivery device 1 may comprise locatorfeatures, such as one or more protrusions 70 and/or one or moreindentations 52. These locator features allow a sensor device (describedbelow) to be releasably attached to the drug delivery device 1 in anaccurate predetermined position.

Drug delivery device 1 may be used for several injection processes untileither insulin container 14 is empty or the expiration date of drugdelivery device 1 (e.g. 28 days after the first use) is reached.Furthermore, before using drug delivery device 1 for the first time, itmay be necessary to perform a so-called “prime shot” to remove air frominsulin container 14 and needle 15, for instance by selecting two unitsof insulin and pressing injection button 11 while holding drug deliverydevice 1 with the needle 15 upwards.

For simplicity of presentation, in the following, it will be exemplarilyassumed that the ejected doses substantially correspond to the injecteddoses, so that, for instance when making a proposal for a dose to beinjected next, this dose equals the dose that has to ejected by the drugdelivery device. Nevertheless, differences (e.g. losses) between theejected doses and the injected doses may of course be taken intoaccount.

FIG. 2a is a schematic illustration of an embodiment of a sensor device2 to be releasably attached to drug delivery device 1 of FIG. 1. Thesensor device 2 may also be referred to herein as a supplementary device2 as it is provided in addition to the drug delivery device andsupplements the features of the drug delivery device. Sensor device 2comprises a housing 20 with a mating unit configured and embrace thehousing 10 of drug delivery device 1 of FIG. 1, so that sensor device 2sits tightly on housing 10 of drug delivery device 1, but isnevertheless removable from drug delivery device 1, for instance whendrug delivery device 1 is empty and has to be replaced. FIG. 2a ishighly schematic, and details of the physical arrangement are describedbelow with reference to FIG. 2 b.

Sensor device 2 contains optical and optional acoustical sensors forgathering information from drug delivery device 1. Information isdisplayed via display unit 21 of sensor device 2. The dosage window 13of drug delivery device 1 is obstructed by sensor device 2 when attachedto drug delivery device 1. Sensor device 2 further comprises at leastone input transducer, illustrated schematically as a button 22. Theseinput transducers 22 allow a user to turn on/off sensor device 2, totrigger actions (for instance to cause establishment of a connection toor a pairing with another device, and/or to trigger transmission ofinformation from sensor device 2 to another device), or to confirmsomething.

FIG. 2b is a schematic illustration of a second embodiment of a sensordevice 2 to be releasably attached to drug delivery device 1 of FIG. 1.Sensor device 2 comprises a housing 20 with a mating unit configured andembrace the housing 10 of drug delivery device 1 of FIG. 1, so thatsensor device 2 sits tightly on housing 10 of drug delivery device 1,but is nevertheless removable from drug delivery device 1. The matingunit may engage with protrusion 70 and/or with indentations 52.

Information is displayed via display unit 21 of sensor device 2. Thedosage window 13 of drug delivery device 1 is obstructed by sensordevice 2 when attached to drug delivery device 1. Sensor device 2further comprises three user input buttons or switches. A first button22 is a power on/off button, via which the sensor device 2 may forinstance be turned on and off. A second button 33 is a communicationsbutton. A third button 34 is a confirm or OK button. The buttons 22, 33,34 may be any suitable form of mechanical switch. These input buttons 22allow a user to turn on/off sensor device 2, to trigger actions (forinstance to cause establishment of a connection to or a pairing withanother device, and/or to trigger transmission of information fromsensor device 2 to another device), or to confirm something.

FIG. 2c is a schematic illustration of a third embodiment of a sensordevice 2 to be releasably attached to drug delivery device 1 of FIG. 1.Sensor device 2 comprises a housing 20 with a mating unit configured andembrace the housing 10 of drug delivery device 1 of FIG. 1, so thatsensor device 2 sits tightly on housing 10 of drug delivery device 1,but is nevertheless removable from drug delivery device 1.

Information is displayed via display unit 21 of the sensor device 2. Thedosage window 13 of drug delivery device 1 is obstructed by sensordevice 2 when attached to drug delivery device 1. Sensor device 2further comprises a touch-sensitive input transducer 35. It alsocomprises a single user input button or switch 22. The button 22 is apower on/off button, via which the sensor device 2 may for instance beturned on and off. The touch sensitive input transducer 35 can be usedto trigger actions (for instance to cause establishment of a connectionto or a pairing with another device, and/or to trigger transmission ofinformation from sensor device 2 to another device), or to confirmsomething.

FIG. 3 shows a schematic view of the sensor device 2 of FIG. 2a, 2b or 2c in a state where it is attached to drug delivery device 1 of FIG. 1.

A plurality of components are contained within the housing 20 of sensordevice 2. The components of the sensor device 2 are controlled by aprocessor 24, which may for instance be a microprocessor, a DigitalSignal Processor (DSP), Application Specific Integrated Circuit (ASIC),Field Programmable Gate Array (FPGA) or the like. Processor 24 executesprogram code (e.g. software or firmware) stored in a program memory 240,and uses a main memory 241, for instance to store intermediate results.Main memory 241 may also be used to store a logbook on performedejections/injections. Program memory 240 may for instance be a Read-OnlyMemory (ROM), and main memory may for instance be a Random Access Memory(RAM).

In embodiments such as those shown in FIG. 2b , processor 24 interactswith a first button 22, via which sensor device 2 may for instance beturned on and off. A second button 33 is a communications button. Thesecond button may be used to trigger establishment of a connection toanother device, or to trigger a transmission of information to anotherdevice. A third button 34 is a confirm or OK button. The third button 34can be used to acknowledge information presented to a user of sensordevice 2. In embodiments such as those shown in FIG. 2c , two of thebuttons 33, 34 may be omitted. Instead, one or more capacitive sensorsor other touch sensors are provided.

Processor 24 controls a display unit 21, which is presently embodied asa Liquid Crystal Display (LCD). Display unit 21 is used to displayinformation to a user of sensor device 2, for instance on presentsettings of drug delivery device 1, or on a next injection to be given.Display unit 21 may also be embodied as a touch-screen display, forinstance to receive user input.

Processor 24 also controls an optical sensor 25, also referred to hereinas an optical sensor assembly 25. In some embodiments the optical sensoris a photosensitive device, such as a camera, for capturing images ofthe dosage window 13, in which a currently selected dose is displayed(by means of numbers printed on the sleeve 19 contained in drug deliverydevice 1, which numbers are visible through the dosage window 13) andproviding information on the captured images to processor 24. Thenprocessor 24 may then perform an Optical Character Recognition (OCR)process on the captured images. In some other embodiments, the opticalsensor 25 is embodied as an OCR reader, that is capable of capturingimages and recognizing characters (e.g. numbers) from the captured imageand to provide this information to processor 24.

Processor 24 also controls a light-source which is an organic lightemitting diode (OLED) 29. The OLED 29 illuminates the dosage window 13as described in detail below. Furthermore, the sensor device 2 maycomprise a lens (e.g. an aspheric lens) arranged in front of the opticalsensor 25, leading to a magnification (e.g. a magnification of more than3:1). The sensor device 2 may also comprise a transparent protectionwindow (not shown) on the underside. The protection window prevents theingress of dust and dirt into the sensor device 2. The light sources maybe configured to illuminate the dosage window 13 through this protectionwindow and the optical sensor 25 views the dosage window 13 through theprotection window.

Processor 24 may further control a photometer 26, that is configured todetermine an optical property of the housing 10 of drug delivery device1, for example a colour or a shading. The optical property may only bepresent in a specific portion of housing 10, for example a colour orcolour coding of sleeve 19 or of an insulin container comprised withindrug delivery device 1, which colour or colour coding may for instancebe visible through a further window in housing 10 (and/or in sleeve 19).Information on this colour is then provided to processor 24, which maythen determine the type of drug delivery device 1 or the type of insulincontained in drug delivery device 1 (e.g. SoloStar Lantus with purplecolour and SoloStar Apidra with blue colour). Alternatively, a cameraunit may be used instead of photometer 26, and an image of the housing,sleeve or insulin container may then be provided to processor 24 todetermine the colour of the housing, sleeve or insulin container bymeans of image processing. Further, one or more light sources may beprovided to improve reading of photometer 26. The light source mayprovide light of a certain wavelength or spectrum to improve colourdetection by photometer 26. The light source may be arranged in such away that unwanted reflections, for example by dosage window 13, areavoided or reduced. In an example embodiment, instead of or in additionto photometer 26, a camera unit may be deployed to detect a code (forinstance a bar code, which may for instance be a one- or two-dimensionalbar code) related to the drug delivery device and/or the medicamentcontained therein. This code may for instance be located on the housing10 or on a medicament container contained in drug delivery device 1, toname but a few examples. This code may for instance indicate a type ofthe drug delivery device and/or the medicament, and/or furtherproperties (for instance a expiration date). The photometer 26 is anoptional feature and may be omitted form the sensor device 2.

Processor 24 may further control (and/or receive signals from) anacoustic sensor 27, which is configured to sense sounds produced by drugdelivery device 1. Such sounds may for instance occur when a dose isdialed by turning dosage knob 12 and/or when a dose is ejected/injectedby pressing injection button 11, and/or when a prime shot is performed.These actions are mechanically similar but nevertheless sounddifferently (this may also be the case for electronic sounds thatindicate these actions). Either the acoustic sensor 27 and/or processor24 may be configured to differentiate these different sounds, forinstance to be able to safely recognize that an injection has takenplace (rather than a prime shot only). The acoustic sensor 27 is anoptional feature and may be omitted form the sensor device 2.

Processor 24 may further control an acoustical signal generator 23,which is configured to produce acoustical signals that may for instancebe related to the operating status of drug delivery device 1, forinstance as feedback to the user. For example, an acoustical signal maybe launched by acoustical signal generator 23 as a reminder for the nextdose to be injected or as a warning signal, for instance in case ofmisuse. Acoustical signal generator may for instance be embodied as abuzzer or loudspeaker. In addition to or as an alternative to acousticalsignal generator 23, also a haptic signal generator (not shown) may beused to provide haptic feedback, for instance by means of vibration. Theacoustical signal generator 23 is an optional feature and may be omittedform the sensor device 2.

Processor 24 may control a wireless unit 28, which is configured totransmit and/or receive information to/from another device in a wirelessfashion. Such transmission may for instance be based on radiotransmission or optical transmission. In some embodiments, the wirelessunit 28 is a Bluetooth transceiver. Alternatively, wireless unit 28 maybe substituted or complemented by a wired unit configured to transmitand/or receive information to/from another device in a wire-boundfashion, for instance via a cable or fibre connection. When data istransmitted, the units of the data (values) transferred may beexplicitly or implicitly defined. For instance, in case of an insulindose, always International Units (IU) may be used, or otherwise, theused unit may be transferred explicitly, for instance in coded form. Insome other embodiments, no means for removing data from the sensordevice 2 are provided.

Processor 24 receives an input from a pen detection switch 30, which isoperable to detect whether the pen 1 is present, i.e. to detect whetherthe sensor device 2 is coupled to the drug delivery device 1. The pendetection switch 30 is an optional feature. A battery 32 powers theprocessor 24 and other components by way of a power supply 31.

The sensor device 2 of FIG. 3 is thus capable of determining informationrelated to a condition and/or use of drug delivery device 1. Thisinformation is displayed on the display 21 for use by the user of thedevice. The information may be either processed by sensor device 2itself, or may at least partially be provided to another device (e.g. ablood glucose monitoring system).

The processor 24 constitutes a processor arrangement. The opticalsensor/OCR reader 25 and the processor 24 together constitute a dosedialed detector operable to detect a dose of medicament dialed and mayalso constitutes a dose delivery determiner for determining that a doseof medicament has been delivered and the quantity of the delivered dose.The processor 24 provides a function of a clock configured to determinea current time.

FIG. 4 is an exploded view of some components of the sensor device 2according to embodiments of the invention, including the optical sensor25 and OLED 29 parts. The optical sensor 25 may be a matrix sensorcomprising an array of light sensitive elements each capable ofmeasuring the intensity of incident light. The matrix sensor may be amonochrome sensor. The optical sensor 25 is mounted on a printed circuitboard (PCB) 401.

A lens assembly 400 may be mounted in front of the optical sensor 25.The focus of the lens assembly 400 may be adjustable. For example, thelens assembly 400 may be provided in two parts which are threadablyengaged such that rotation of one part causes movement of an opticalelement along an optical axis. Both the lens assembly 400 and opticalsensor 25 may be mounted on the same PCB 401. The lens assembly 400 mayprovide magnification of incident light onto the optical sensor 25. Insome embodiments a lens assembly 400 is not needed and can be omitted.

FIG. 4 also shows an internal carrier member 402 located between theoptical sensor 25 and the OLED 29. The internal carrier member 402 mayserve several purposes, such as to protect and support the PCB 401,optical sensor 25, lens assembly 400 and other hardware components ofthe sensor device 2. The internal carrier member 402 may also ensurecorrect separation distance between the optical sensor 25 and externalhousing 20 of the sensor device 2 and block any light from reaching theoptical sensor 25 directly from the OLED 29. The internal carrier member402 has a hole arranged to receive the lens assembly 400 (if present)and to allow light reflected from the surface of the drug deliverydevice 1 to enter the sensor device 2 and be received by the opticalsensor 25.

The OLED 29 is constructed from a transparent material. The OLED 29comprises a first electrode 405, a second electrode 406 and a centrallayer 408 located between the first and second electrodes 405, 406. Allof these layers are transparent to visible light. The OLED 29 may alsocomprise a substrate (not shown). In some embodiments, the firstelectrode 405 is the anode and the second electrode 406 is the cathode.The central layer 408 is comprised of one or more layers of organicsemiconductor. In some embodiments, the central layer 408 comprises aconductive layer and an emissive layer. In some other embodiments, oneor more additional organic semiconductor layers may be interposedbetween the conductive and emissive layers. This may be done to alterthe electronic profile of the central layer 408. In yet furtherembodiments, the central layer 408 may comprise a single organic layerwhich is a graded heterojunction. In any case, the central layer 408 isso arranged that when a voltage is applied across the electrodes 405,406, recombination in the central layer 408 causes light to be emittedfrom the central layer.

When the sensor device 2 is attached to the drug delivery device 1 andis in use, light is emitted from the central layer 408, through thetransparent first electrode 405 and out towards the surface of the drugdelivery device. As the second electrode 406 is also transparent, lightis also emitted out through the second electrode towards the internalcarrier member 402. In some embodiments, a reflective layer 404 may bedisposed between the second electrode 406 and the internal carriermember 402. The reflective layer 404 may be a mirror foil. Thisreflective layer 404 ensures that light which escapes the OLED 29through the second electrode 406 is reflected back into the OLED so thatit can be emitted through the first electrode 405. In some embodiments,the reflective layer 404 may be the substrate onto which the OLED 29 isformed. The reflective layer 404 has a hole aligned with the hole in theinternal carrier member 402 in order to allow light reflected from thesurface of the drug delivery device 1 to enter the sensor device 2 andbe received by the optical sensor 25. In some other embodiments, thereflective layer 404 may be adhered to the internal carrier member 402or the internal carrier member 402 may be coated with a reflectivelayer. The reflective layer 404 is an optional feature which may beomitted.

The central layer 408 of the OLED 29 comprises a region 37 without anyorganic semiconductor layers. This region 37 is arranged underneath theholes in the internal carrier member 402 and reflective layer 404 (ifpresent) so as to be aligned with the lens assembly 400 (if present) andoptical sensor 25. As this region 37 does not have any organicsemiconductor layers, no light is emitted from this region. The region37 may be made of any transparent material, such as a plastic, which ispreferably an insulator (non-conducting). In some other embodiments, theregion 37 without any organic semiconductor layers comprises a holeextending through the body of the OLED 29, i.e. through the firstelectrode 405, second electrode 406, and central layer 408. Although theOLED 29 is transparent, providing a region 37 which does not emit lightand through which the optical sensor 25 views the drug delivery device 1avoids the sensor 25 being saturated by the emitted light, which wouldprevent the sensor from obtaining a high contrast image of the surfaceof the drug delivery device. The region 37 without any organicsemiconductor layers may be any suitable shape, such as square,rectangular (as shown in FIGS. 4 and 6), any other regular polygon,circular, oval or a mixture of straight and curved edges.

One or more brightness enhancing films (not shown) may be provided, forexample as a layer deposited on the first electrode 405 or on the secondelectrode 406. The brightness enhancing films may be, for example prismfilms or reflective films. These may increase the output brightness ofthe OLED 29 and/or reduce the power consumption of the sensor device 2for a given brightness. One or more diffuser foils may also be providedto increase the homogeneity of the output light and therefore thehomogeneity of the illumination of the drug delivery device 1.Alternatively a single film which both enhances brightness and causesdiffusion of the light may be provided.

A number of different arrangements of the OLED 29 and region 37 withoutany organic semiconductor layers may be used, as will now be describedwith reference to FIGS. 5A to 9. In these Figures, like numerals areused for like parts, and these parts are not described again in detail.

FIG. 5A is a schematic cross-section view showing an arrangement similarto that of FIG. 4. The internal carrier member 402, reflective layer 404and other components are omitted for clarity. FIG. 5A shows the opticalsensor 25 and lens assembly 400 positioned above the OLED 29. The OLED29 of FIG. 5A is constructed of planar layers and has upper and lowersurfaces which are flat and parallel to each other. The region 37without any light out-coupling structure is located directly underneaththe lens assembly 400.

Diffuse light is emitted from the regions of the central layer 408 ofthe OLED 29 having the organic semiconductor layers when a voltage isapplied across the electrodes 405, 406. This light passes through thedosage window 13 and illuminates the number sleeve 19 of the drugdelivery device 1. Light reflected from the number sleeve 19 passedthrough the region 37 without any organic semiconductor layers, throughthe lens assembly 400 and is received by the optical sensor 25. Theoptical sensor 25 then sends signals to the processor 24.

FIG. 5B shows another embodiment of the sensor device 2 in which theOLED 29 is curved. Unlike other light emitting structures, OLEDs canreadily be manufactured to be flexible. Having a curved OLED 29increases the evenness of the illumination of the number sleeve 19, asthe number sleeve has a cylindrical surface. Having a curved OLED 29also reduces reflections from the dosage window 13 and protection window(if present), therefore increasing the efficiency of the illuminationand preventing the occurrence of bright spots which may impair thecapturing of a high quality image by the optical sensor 25. Preferably,the curvature of the OLED 29 is such that it is concentric with thenumber sleeve 19 and/or dosage window 13 when the sensor device 2 isattached to the drug delivery device 1.

FIG. 6 is a plan view of an OLED 29 suitable for use in embodiments ofthe present invention. The central layer 408 of the OLED 29 comprisesone or more organic semiconductor layers, represented by dots. Arectangular region 37 without any organic semiconductor layers isprovided approximately centrally in the OLED 29. This region 37 maycomprise a transparent material. The optical properties of the region37, such as the refractive index and opacity may be chosen based on theoptical sensor 25, lens assembly 400 and other components so as to allowthe optical sensor 25 to capture a high quality, high contrast image ofthe number sleeve 19. In some other embodiments, this region 37comprises a hole extending through the whole body of the OLED 29, i.e.the region 37 is comprised of air. Although a rectangular region 37 isshown, any suitable shape may be used, such as square, any other regularpolygon, circular, oval or a mixture of straight and curved edges. TheOLED 29 of FIG. 6 may be a planar film, or may be curved as shown inFIGS. 5A and 5B respectively.

FIG. 7 is an exploded view of some components of the sensor device 2according to embodiments of the invention. FIG. 7 comprises the samecomponents as described above with reference to FIG. 4. The OLED 29shown in FIG. 7 has a region 37 without any light out-coupling structurewhich is comprised of a hole in the OLED. Providing a hole 37 in theOLED 29 has advantages over the transparent region shown in FIG. 4, inthat there is zero distortion of the reflected light which passesthrough the hole 37. However, using a transparent piece of material forthe region 37 may increase the efficiency of the illumination as lightcan propagate through and undergo total internal reflection within thisregion 37. Thus the power requirements of the sensor device 2 may bereduced while providing the same illumination brightness relative to aOLED with a hole.

FIG. 8 shows in schematic cross-section a further embodiments of thesensor device 2. In FIG. 8, the hole in the OLED 29 is large enough toaccommodate the lens assembly 400. This may result in a space savingwithin the sensor device 2 and/or reduce the cost and complexity of theoptical elements in the lens assembly. This arrangement may also allow alower level of illumination to be used as the lens assembly 400 andoptical sensor 25 are closer to the surface of the number sleeve 19.Unwanted distortion and reflection effects produced by the dosage window13 and by the protection window (if present) may also be mitigated byplacing the lens assembly 400 and optical sensor 25 closer to the window13.

FIG. 9 is a flowchart 900 of a method in which the present invention isembodied. In step 901, a user attaches the sensor device 2 to the drugdelivery device 1. The pen detection switch 30 (if present) detects thatthe sensor device 2 has been attached to the drug delivery device 1.This may cause the sensor device 2, including the OLED 29, to be poweredon. Alternatively, or if the detect switch 30 is not present, the userpresses the power button 22 to switch the sensor device on. At this timethe OLED 29 and optical sensor 25 are also powered on (step 902).

The processor 24 of sensor device 2 may then execute a program stored inprogram memory 240 to determine a dose which is dialed into the drugdelivery device 1 to which the sensor device is attached.

In a step 903, a sub-image is captured by an optical sensor such asoptical sensor 25 of sensor device 2. The captured sub-image is forinstance an image of at least a part of the dosage window 13 of drugdelivery device 1, in which a currently selected dose is displayed (e.g.by means of numbers and/or a scale printed on the sleeve 19 of drugdelivery device 1, which is visible through the dosage window 13). Forinstance, the captured sub-image may have a low resolution and/or onlyshow a part of the part of sleeve 19 which is visible through dosagewindow 13. For instance, the captured sub-image either shows the numbersor the scale printed on the part of sleeve 19 of drug delivery device 1which is visible through dosage window 13. The OLED 29 which causesillumination of the number sleeve 19 may be operated in a dimmer andtherefore lower power mode for the purpose of sub-image capture. Aftercapturing an image, it is, for instance, further processed as follows:

Division by a previously captured background image;

Binning of the image(s) to reduce the number of pixels for furtherevaluations;

Normalization of the image(s) to reduce intensity variations in theillumination;

Sheering of the image(s); and/or

Binarization of the image(s) by comparing to a fixed threshold.

Several or all of these steps may be omitted if applicable, for instanceif a sufficiently large optical sensor (e.g. a sensor with sufficientlylarge pixels) is used.

In a step 904, it is determined whether or not there is a change in thecaptured sub-image. For instance, the currently captured sub-image maybe compared to the previously captured sub-image(s) in order todetermine whether or not there is a change. Therein, the comparison topreviously captured sub-images may be limited to the sub-image of thepreviously captured sub-images that was captured immediately before thecurrent sub-image was captured and/or to the sub-images of thepreviously captured sub-images that were captured within a specifiedperiod of time (e.g. 0.1 seconds) before the current sub-image wascaptured. The comparison may be based on image analysis techniques suchas pattern recognition performed on the currently captured sub-image andon the previously captured sub-image. For instance, it may be analyzedwhether the pattern of the scale and/or the numbers visible through thedosage window 13 and shown in the currently captured sub-image and inthe previously captured sub-image is changed. For instance, it may besearched for patterns in the image that have a certain size and/oraspect ratio and these patterns may be compared with previously savedpatterns. Steps 903 and 904 may correspond to a detection of a change inthe captured image.

If it is determined in step 904 that there is a change in the sub-image,step 903 is repeated. Otherwise in a step 905, an image is captured byan optical sensor such as optical sensor 25 of sensor device 2. Thecaptured image is for instance an image of the dosage window 13 of drugdelivery device 1, in which a currently selected dose is displayed (e.g.by means of numbers and/or a scale printed on the sleeve 19 of drugdelivery device 1, which is visible through the dosage window 13). Forinstance, the captured image may have a resolution being higher than theresolution of the captured sub-image. The captured image at least showsthe numbers printed on the sleeve 19 of drug delivery device 1 which arevisible through the dosage window 13.

In a step 906, optical character recognition (OCR) is performed on theimage captured in step 905 in order to recognize the numbers printed onthe sleeve 19 of drug delivery device 1 and visible through the dosagewindow 13, because these numbers correspond to the (currently) selecteddose. This step may be performed by the optical sensor 25 if it is soprogrammed, or alternatively the optical sensor 25 may send signalsrepresenting light intensity values to the processor 24 and theprocessor may then perform the OCR process. In accord to the recognizednumbers, the selected dose is determined, for instance by setting avalue representing the selected dose to the recognized numbers.

In a step 907, it is determined whether or not there is a change in thedetermined selected dose and, optionally, whether or not the determinedselected dose does not equal zero. For instance, the currentlydetermined selected dose may be compared to the previously determinedselected dose(s) in order to determine whether or not there is a change.Therein, the comparison to previously determined selected dose(s) may belimited to the previously determined selected dose(s) that weredetermined within a specified period of time (e.g. 3 seconds) before thecurrent selected dose was determined. If there is no change in thedetermined selected dose and, optionally, the determined selected dosedoes not equal zero, the currently determined selected dose isreturned/forwarded for further processing (e.g. to processor 24).

Thus, the selected dose is determined if the last turn of the dosageknob 12 is more than 3 seconds ago. If the dosage knob 12 is turnedwithin or after these 3 seconds and the new position remains unchangedfor more than 3 seconds, this value is taken as the determined selecteddose.

A standard drug delivery device 1, in particular an insulin device, maybe connected with a blood glucose monitoring system in a useful andproductive way. The sensor device 2 may provide this connection,assuming the blood glucose monitoring system has wireless or othercommunication capabilities. The benefits from the connection between theblood glucose monitoring and an insulin drug delivery device are interalia the reduction of mistakes by the user of the drug delivery deviceand a reduction of handling steps—no more manual transfer of theinjected insulin unit to a blood glucose monitoring is required, inparticular to a blood glucose monitoring system with functionality ofproviding guidance for the next dose based on the last dose injected andlatest blood glucose values.

As described with reference to exemplary embodiments above, when auser/patient gets a new insulin pen, the user attaches the sensor device2 to the pen. The sensor device reads out the injected dose. It may alsotransfer it to a blood glucose monitoring system with insulin titrationcapabilities. For patients taking multiple insulins, the sensor device 2recognizes the device structure to the insulin type and may alsotransmit this piece of information to the blood glucose monitoringsystem.

In example embodiments, the information shown on a display, for exampleLCD display 21 of FIGS. 2a-c and 3, may also be converted to a soundsignal played to a user through a speaker, for example by atext-to-speech functionality implemented by processor 24 using theacoustical signal generator 23. Thus, a user with impaired vision mayhave improved access to the information of sensor device 2, such as adialed dose, a recommended dose, a recommended time for administrationand/or the like.

When using embodiments of the present invention, the user inter alia hasthe following advantages:

The user can use the most convenient disposable insulin injector.

The sensor device is attachable and detachable (reusable).

Injected dose information may be transferred to the blood glucosemonitoring system automatically (no more transfer mistakes). Improveddose guidance may result from this as the blood glucose monitoringsystem calculates the dose to be taken.

Keeping of a manual data logbook may not be needed any more.

Furthermore, when deploying the sensor device proposed by the presentinvention, patients may also be reminded of injecting their next dose byreceiving an alarm signal, for instance, after an appropriate time aftera first dose of a medicament (for instance insulin or heparin) has beeninjected.

Injected dose information may be transferred to any computerized system,for instance as input for any dose calculation or any other applicabletherapeutic guidance calculation, or for the creation of an alarmsignal, for instance to remind the user of taking the next dose.

The invention claimed is:
 1. A sensor device configured to be attachedto a drug delivery device, the sensor device comprising: a housingconfigured to be attached to the drug delivery device; a curved OLEDhaving a transparent first electrode, a transparent second electrode,and a central layer disposed between the first and second transparentelectrodes, the central layer comprising at least one organic layer, theat least one organic layer being an integral piece and configured to,when the housing is attached to the drug delivery device, emit diffuselight through the first transparent electrode; and an optical sensorarranged to, when the housing is attached to the drug delivery device,receive at least part of the diffuse light reflected from a surface ofthe drug delivery device, wherein the central layer of the curved OLEDhas a region without the at least one organic layer and wherein theoptical sensor is arranged, when the housing is attached to the drugdelivery device, to view a predetermined area of the surface of the drugdelivery device through the region without the at least one organiclayer, and wherein a light emitting surface of the curved OLED isconcave, wherein the light emitting surface of the curved OLED isconfigured to be substantially concentric with a cylindrical surface ofthe drug delivery device when the housing is attached to the drugdelivery device.
 2. The sensor device according to claim 1, wherein thefirst transparent electrode is an anode and the second transparentelectrode is a cathode.
 3. The sensor device according to claim 1,wherein the sensor device further comprises a reflective backing layeradjacent the second transparent electrode configured to reflect anylight which escapes the curved OLED through the second transparentelectrode back into the curved OLED.
 4. The sensor device according toclaim 1, wherein the region without the at least one organic layercomprises a transparent material.
 5. The sensor device according toclaim 1, wherein the region without the at least one organic layercomprises a hole in the central layer and wherein the curved OLEDcomprises corresponding holes in the first and second transparentelectrodes such that a hole is formed through a body of the curved OLED.6. The sensor device according to claim 5, wherein the sensor devicefurther comprises a lens assembly configured to focus light reflectedfrom the surface of the drug delivery device onto the optical sensor. 7.The sensor device according to claim 6, wherein the lens assembly isdisposed in the hole in through the body of the curved OLED such that afirst end of the lens assembly is the same as or a smaller distance fromthe surface of the drug delivery device than the first transparentelectrode.
 8. The sensor device according to claim 1, wherein the sensordevice further comprises a processor configured to receive lightintensity signals from the sensor device and to perform an opticalcharacter recognition process on the received light intensity signals todetermine a number present on the surface of the drug delivery device.9. The sensor device according to claim 8, wherein the processor isfurther configured to determine an amount of medicament programmed intothe drug delivery device and to cause the amount of medicament to bedisplayed on a display device of the drug delivery device.
 10. Thesensor device according to claim 1, wherein the curved OLED furthercomprises one or more brightness enhancing layers.
 11. The sensor deviceaccording to claim 1, wherein the drug delivery device is a pen typeinjection device.
 12. A system comprising the sensor device of claim 1and a drug delivery device configured to be attached to the sensordevice, wherein the drug delivery device comprises: a housing to receivea cartridge, and an actuator operable to deliver a dose of drug from thecartridge.
 13. A system comprising: a drug delivery device comprising: ahousing to receive a cartridge, and an actuator operable to deliver adose of drug from the cartridge, and a sensor device configured to beattached to the drug delivery device, the sensor device comprising: acurved OLED having a first electrode, a second electrode and a centrallayer disposed between the first and second electrodes, the centrallayer comprising at least one organic layer, the at least one organiclayer configured to emit light through the first electrode; and anoptical sensor arranged to receive light reflected from a surface of thedrug delivery device, wherein the central layer of the curved OLED has aregion without the at least one organic layer and wherein the opticalsensor is arranged, when the sensor device is attached to the drugdelivery device, to view a predetermined area of the surface of the drugdelivery device through the region without the at least one organiclayer, wherein a light emitting surface of the curved OLED is concave,and wherein the light emitting surface of the curved OLED is configuredto be substantially concentric with the surface of the drug deliverydevice when the sensor device is attached to the drug delivery device.